Execution and initialisation of processes for a device

ABSTRACT

Systems and methods for detecting when a device is placed into an operational position are disclosed. Upon determination that the device is in the operational position, one or more processes can be executed. Execution or initialization of the processes upon detection of the operational position provides for the determination of optimal settings than would otherwise be determined if the processes automatically executed before detection of the operational position. Further aspects of the present disclosure relate to determining when the device is no longer in an operational position upon which time the execution of the processes are terminated. The settings in place upon termination can be saved and reapplied the next time the device is in the operational position.

BACKGROUND

Hearing loss, which can be due to many different causes, is generally oftwo types: conductive and sensorineural. In many people who areprofoundly deaf, the reason for their deafness is sensorineural hearingloss. Those suffering from some forms of sensorineural hearing loss areunable to derive suitable benefit from auditory prostheses that generatemechanical motion of the cochlea fluid. Such individuals can benefitfrom implantable auditory prostheses that stimulate nerve cells of therecipient's auditory system in other ways (e.g., electrical, optical,and the like). Cochlear implants are often proposed when thesensorineural hearing loss is due to the absence or destruction of thecochlea hair cells, which transduce acoustic signals into nerveimpulses. Auditory brainstem implants might also be proposed when arecipient experiences sensorineural hearing loss if the auditory nerve,which sends signals from the cochlear to the brain, is severed or notfunctional.

Conductive hearing loss occurs when the normal mechanical pathways thatprovide sound to hair cells in the cochlea are impeded, for example, bydamage to the ossicular chain or the ear canal. Individuals sufferingfrom conductive hearing loss can retain some form of residual hearingbecause some or all of the hair cells in the cochlea function normally.

Individuals suffering from conductive hearing loss often receive aconventional hearing aid. Such hearing aids rely on principles of airconduction to transmit acoustic signals to the cochlea. In particular, ahearing aid typically uses an arrangement positioned in the recipient'sear canal or on the outer ear to amplify a sound received by the outerear of the recipient. This amplified sound reaches the cochlea causingmotion of the perilymph and stimulation of the auditory nerve.

In contrast to conventional hearing aids, which rely primarily on theprinciples of air conduction, certain types of hearing prosthesescommonly referred to as bone conduction devices, convert a receivedsound into vibrations. The vibrations are transferred through the skullto the cochlea causing motion of the perilymph and stimulation of theauditory nerve, which results in the perception of the received sound.Bone conduction devices are suitable to treat a variety of types ofhearing loss and can be suitable for individuals who cannot derivesufficient benefit from conventional hearing aids.

SUMMARY

Aspects of the present disclosure relate to systems and methods fordetecting when a medical device is placed into an operational positionon a recipient. Upon determination that the device is in the operationalposition, one or more processes can be executed. Execution of theprocesses upon detection of the operational position provides for thedetermination of optimal settings than would otherwise be determined ifthe processes automatically executed upon device initialization. Furtheraspects of the present disclosure relate to determining when the deviceis no longer in an operational position upon which time the execution ofthe processes are terminated. The settings in place upon termination canbe saved and reapplied the next time the device is in the operationalposition.

Further aspects of the present disclosure relate to a feedback algorithmthat reduces the likelihood of generating audible artefacts. Inexamples, the feedback algorithm executes with an initial phase thatemploys a faster adaptation speed. During the initial phase, theamplitude of the device may be incrementally increased. Upon completionof the initial phase, the feedback algorithm may be adjusted to employan operational adaptation speed.

This summary is provided to introduce a selection of concepts in asimplified form that are further described below in the DetailedDescription. This summary is not intended to identify key features oressential features of the claimed subject matter, nor is it intended tobe used to limit the scope of the claimed subject matter.

BRIEF DESCRIPTION OF THE DRAWINGS

The same number represents the same element or same type of element inall drawings.

FIG. 1 depicts a partial cross-sectional schematic view of an activetranscutaneous bone conduction device worn on a recipient.

FIG. 2 is a schematic diagram of a percutaneous bone conduction device.

FIG. 3 depicts a partial cross-sectional schematic view of a passivetranscutaneous bone conduction device worn on a recipient.

FIG. 4 is a partial view of a direct acoustic stimulator worn on arecipient.

FIG. 5 is a partial view of a behind-the-ear auditory prosthesis worn ona recipient.

FIG. 6 is a schematic diagram of a totally implantable cochlear implant.

FIG. 7 is an exemplary method for executing a process upon detectingthat a device is in an operational position.

FIG. 8 is an exemplary method for executing a feedback algorithm upondetecting that a sound processor is in an operational position.

FIG. 9 is an exemplary method for performing phased feedback reduction.

FIG. 10 illustrates one example of a suitable operating environment inwhich one or more of the present examples can be implemented.

DETAILED DESCRIPTION

Various types of devices, such as medical devices that operate on and/orwithin a recipient or such as consumer electronic devices that generateor assist in generation of audible output, utilize processes thatexecute after the devices are turned on and that could execute beforethe devices are put into the location or one of the locations thedevices are intended to operate in (e.g., an operational position), butthat operate more effectively and/or efficiently when executed after thedevices or one or more components of the devices are put into anoperational position. Non-limiting examples of such processes includingbeam forming and feedback algorithms. The operation of such processes iseffectible by a position of the devices or one or more components of thedevices.

For instance, many recipients of auditory prostheses can experiencediscomfort during initialization of the auditory prosthesis. Thediscomfort can be the result of audible artifacts that are generatedduring the establishment of a stable feedback loop for the auditoryprosthesis. Feedback is a major concern when increasing gain in anysystem with a microphone or similar sensor in the vicinity of the outputtransducer. Problematic feedback occurs when the gain (i.e., amplitude)of the device is larger than the attenuation in the feedback loopoutside the device, i.e., a negative remaining gain margin, which isoften the state of an auditory prosthesis during initialization of thedevice.

One common method to reduce feedback is to identify when feedback occursand cancel out the feedback signal with an adaptive filter in a feedbackalgorithm. Some pre-filtering or other start point criteria are oftenused to adapt faster with less audible artefacts. In existing systems, afeedback algorithm is executed as soon as an auditory prosthesis isinitialized and before it is placed in an operational position. Forexample, auditory prostheses are generally initialized while still in arecipient's hand and then subsequently placed in an operationalposition, e.g., on the recipient's head, within the recipient's ear,etc. However, because the establishment of the feedback loop isperformed while an auditory prosthesis (in its entirety) or a componentof the auditory prosthesis, e.g., a sound processor, is in therecipient's hand, the established feedback loop is not optimally set foroperational performance. This results in a sub-optimal result and/or asub-optimal experience, e.g., audible artefacts.

For instance, when a feedback algorithm is first initialized, theadaptation speed of the feedback algorithm can be set to an aggressive,e.g., quicker, speed. The aggressive adaptation speed can result in thegeneration of audible artifacts, e.g., chirps or tones, that can causediscomfort or embarrassment to a recipient.

Aspects of the present disclosure relate to detecting when a componentof an auditory prosthesis, e.g., an external device for an implantableprosthesis, a hearing aid, etc., is placed in an operational positionfor the recipient. Upon detection of the placement, a feedback algorithmhaving a faster initial adaptation speed is executed for a limited time.In this way the auditory prosthesis adapts to address, e.g., changeswithin the recipient, where a portion of the feedback path exists insome embodiments, since the auditory prosthesis was fitted to therecipient and/or was last in an operational position. A result isdetermination of optimal operational settings. In embodiments, in orderto reduce the likelihood of audible artefacts, the initial feedbackalgorithm is performed during a ramp up of volume (e.g., gain oramplitude) which allows the feedback algorithm to adapt before high gainintroduces a feedback problem.

Additional embodiments relate to initialization settings based on afeedback measurement setting, for example using a pre-filter or allowingthe adaptive feedback algorithm to start from a previously determinedfeedback setting, for example using frequency based upon air delay,filter dynamics, step size, etc. In doing so, the difference between theinitialization settings and any changes to the feedback path since theinitial fitting of the auditory prosthesis will be reduced, therebyallowing for the use of a slower adaptation speed during aninitialisation stage. A slower adaptation speed reduces the likelihoodof instability and/or audible artefacts, thereby enhancing therecipient's experience. For instance, settings can be smoothed and/oraveraged over time. In alternative embodiments, samples of the filtersettings are saved during this first initialization time and an averagedfilter is then used as starting point for the adaptive filter during asubsequent initialization.

Various devices that can employ and benefit from the systems and methodsdisclosed herein will now be described. While specific devices aredescribed herein, one of skill in the art will appreciate that othertypes of devices can employ the aspects disclosed herein withoutdeparting from the scope of this disclosure. For instance, the type ofprocesses executed upon placement of an auditory prosthesis in anoperational position can vary depending on the type of the auditoryprosthesis. Some types of auditory prostheses, such as certain cochlearimplants, do not have problems with feedback, but do utilize beamforming algorithms. Like feedback algorithms, beam forming algorithmsare best initialized while the device executing such is set in anoperational position. Other auditory prostheses (e.g., traditionalhearing aids, bone conduction devices, direct acoustic stimulators,middle ear devices, electro-acoustic implants, etc.), do have problemswith feedback and some utilize beam forming algorithms. Such devicesideally initialize feedback and beamforming algorithms while theauditory prostheses, or a component of the auditory prosthesis, is setin an operational position, as described herein.

FIG. 1 depicts a partial cross-sectional schematic view of an activetranscutaneous bone conduction device 100 worn on a recipient. Theactive transcutaneous bone conduction device 100 includes an externaldevice 140 and an implantable component 150. The bone conduction device100 of FIG. 1 is an active transcutaneous bone conduction device in thatthe vibrating actuator 152 is located in the implantable component 150.Specifically, a vibratory element in the form of vibrating actuator 152is located in an encapsulant 154 of the implantable component 150. Inthe various examples described herein, implanted encapsulants 154 can bebiocompatible ceramic, plastic, or other materials. In an example, muchlike the vibrating actuator 152 described below with respect totranscutaneous bone conduction devices, the vibrating actuator 152 is adevice that converts electrical signals into vibration.

External component 140 includes a sound input element 126 that convertssound into electrical signals. Specifically, the transcutaneous boneconduction device 100 provides these electrical signals to a soundprocessor (not shown) that processes the electrical signals, and thenprovides those processed signals to the implantable component 150through the skin 132, fat 128, and muscle 134 of the recipient via amagnetic inductance link. In this regard, a transmitter coil 142 of theexternal component 140 transmits these signals to implanted receivercoil 156 located in an encapsulant 158 of the implantable component 150.Successful communications between transmitter coil 142 and receiver coil156 can be indicative of the external component 140 being in anoperational position (and in some embodiments, trigger, e.g., a‘coil-on’ alert). If the coils are too far apart, too misaligned,shifted, etc., such successful communications are not possible. Themargin for error in terms of placement of the transmitter coil 142 ofthe external component 140 in relation to the implanted receiver coil156 depends on the characteristics of a given device.

The vibrating actuator 152 converts the electrical signals intovibrations. In another example, signals associated with external soundscan be sent to an implanted sound processor disposed in the encapsulant158, which then generates electrical signals to be delivered tovibrating actuator 152 via electrical lead assembly 160. The vibratingactuator 152 is mechanically coupled to the encapsulant 154. Encapsulant154 and vibrating actuator 152 collectively form a vibrating element.The encapsulant 154 is substantially rigidly attached to bone fixture146B, which is secured to bone 136. A silicone layer 154A can bedisposed between the encapsulant 154 and the bone 136. In this regard,encapsulant 154 includes through hole 162 that is contoured to the outercontours of the bone fixture 146B. Screw 164 is used to secureencapsulant 154 to bone fixture 146B. As a result of the screw 164 andthe bone fixture 146B, the vibrating actuator 152 maintains a relativelystable position in relation to the recipient's head. As result of thisrelatively stable position, portions of the feedback path within therecipient are relatively consistent between cycles of operation of theactive transcutaneous bone conduction device 100. Less stable locationalrelationships between an actuator and a recipient might be found forother types of auditory prostheses, such as hearing aids and passivetranscutaneous bone conduction devices, which could negatively impactbeam forming and/or feedback algorithms.

FIG. 2 is a schematic diagram of a percutaneous bone conduction device200. Sound 207 is received by sound input element 252. In somearrangements, sound input element 252 is a microphone configured toreceive sound 207, and to convert sound 207 into electrical signal 254.Alternatively, sound 207 is received by sound input element 252 as anelectrical signal. As shown in FIG. 2 , electrical signal 254 is outputby sound input element 252 to electronics module 256. Electronics module256 is configured to convert electrical signal 254 into adjustedelectrical signal 258. As described below in more detail, electronicsmodule 256 can include a sound processor, control electronics,transducer drive components, and a variety of other elements.

As shown in FIG. 2 , transducer 260 receives adjusted electrical signal258 and generates a mechanical output force in the form of vibrationsthat is delivered to the skull of the recipient via anchor system 262,which is coupled to bone conduction device 200. Delivery of this outputforce causes motion or vibration of the recipient's skull, therebyactivating the hair cells in the recipient's cochlea (not shown) viacochlea fluid motion. A power module 270 provides electrical power toone or more components of bone conduction device 200. For ease ofillustration, power module 270 has been shown connected only to userinterface module 268 and electronics module 256. However, it should beappreciated that power module 270 can be used to supply power to anyelectrically powered circuits/components of bone conduction device 200.

User interface module 268, which is included in bone conduction device200, allows the recipient to interact with bone conduction device 200.For example, user interface module 268 can allow the recipient to adjustthe volume, alter the speech processing strategies, power on/off thedevice, etc. In the example of FIG. 2 , user interface module 268communicates with electronics module 256 via signal line 264.

Bone conduction device 200 can further include external interface module266 that can be used to connect electronics module 256 to an externaldevice, such as a fitting system. Using external interface module 266,the external device, can obtain information from the bone conductiondevice 200 (e.g., the current parameters, data, alarms, etc.), and/ormodify the parameters of the bone conduction device 200 used inprocessing received sounds and/or performing other functions.

In the example of FIG. 2 , sound input element 252, electronics module256, transducer 260, power module 270, user interface module 268, andexternal interface module 266 have been shown as integrated in a singlehousing, referred to as an auditory prosthesis housing or an externalportion housing 250. However, it should be appreciated that in certainexamples, one or more of the illustrated components can be housed inseparate or different housings. Similarly, it should also be appreciatedthat in such examples, direct connections between the various modulesand devices are not necessary and that the components can communicate,for example, via wireless connections. Additionally, the bone conductiondevice 200 can include a sensor 276 that can be used to detect when thedevice 200 is in an operational position on the recipient. For example,the sensor 276 can detect the presence of a corresponding emitter (RFID,Bluetooth, Wi-Fi, etc.) located on the anchor system 262. Alternatively,the sensor 276 can detect a condition of the transducer module 260(e.g., the load on the transducer module) indicative of that componentbeing engaged with the anchor system 262. Such detection can then becommunicated to the electronics module 256 that the device is in anoperational position. The sensor 276 can also be a proximity or positionsensor, or may be a button, switch, or other mechanical element that candetect a connection between the transducer module 260 and the anchorsystem 262.

Typically, the external portion housing 250 is attached to the anchorsystem 262 in a relatively rigid manner via a so called snap coupling.When in operation, the external portion housing 250 is snapped to theanchor system 262. As a result of this attachment, the external portionhousing 250 (and the actuator or vibrator contained therein) maintains arelatively stable position in relation to the recipient's head, e.g.,the external portion housing 250 is prevented from shifting duringoperation and from one cycle of operation to the next. As result of thisrelatively stable position, portions of the feedback path are relativelyconsistent between cycles of operation of the percutaneous boneconduction device 200. Less stable locational relationships might befound for other types of auditory prostheses, such as hearing aids andpassive transcutaneous bone conduction devices. Note however that insome such embodiments, the external portion housing 250 is able torotate about an axis of the anchor system 262. That is to stay that atthe start of each cycle of operation, the external portion housing 250might be rotated more or less (in relation to a hypothetical zerodegrees of rotation) than in the previous cycle of operation, which canhave in impact or beam forming algorithms, particularly theinitialization of the beam forming algorithm.

FIG. 3 depicts an example of a passive transcutaneous bone conductiondevice 300 that includes an external portion 304 and an implantableportion 306. The device 300 of FIG. 3 is a passive transcutaneous boneconduction device in that a vibrating actuator 308 is located in theexternal portion 304. In such devices, there are typically no activeelectrical or mechanical components in the implanted portion 306.

Vibrating actuator 308 is located in housing 310 of the externalcomponent, and is coupled to a pressure or transmission plate 312. Thepressure plate 312 can be in the form of a permanent magnet and/or inanother form that generates and/or is reactive to a magnetic field, orotherwise permits the establishment of magnetic attraction between theexternal portion 304 and the implantable portion 306 sufficient to holdthe external portion 304 against the skin of the recipient. Magneticattraction can be further enhanced by utilization of a magneticimplantable plate 316 that is secured to the bone 336. Single magnetsare depicted in FIG. 3 . In alternative examples, multiple magnets inboth the external portion 304 and implantable portion 306 can beutilized. In a further alternative example the pressure plate 312 caninclude an additional plastic or biocompatible encapsulant (not shown)that encapsulates the pressure plate 312 and contacts the skin 332 ofthe recipient. The device 300 may include a sensor or other component330, such as those described above, so as to detect when the device 300is in an operational position. These sensors or components 330 can,e.g., detect RFID, Bluetooth, or WiFi emitted from an implantableportion 306. Alternatively, the sensor 330 can detect a magnetic fieldindicative of the device 300 being in an operational position. Inanother example, the sensor 330 can be a button or mechanical switch orstructure that is depressed when the device 300 is in contact with theskin 332. The sensor 330 may also be disposed within the device 300,discrete from the plate, and detect a load condition on the vibratingactuator 308 that is indicative of the pressure plate 312 being incontact with the skin 332. In the illustrated embodiment of FIG. 3 , thesensor 330 is disposed on the pressure plate 312, but in otherembodiments, the sensor 330 is disposed elsewhere, such as elsewherewithin the device 300.

In an example, the vibrating actuator 308 is a device that convertselectrical signals into vibration. In operation, sound input element 326converts sound into electrical signals. Specifically, the transcutaneousbone conduction device 300 provides these electrical signals tovibrating actuator 308, via a sound processor (not shown) that processesthe electrical signals, and then provides those processed signals tovibrating actuator 308. The vibrating actuator 308 converts theelectrical signals into vibrations. Because vibrating actuator 308 ismechanically coupled to pressure plate 312, the vibrations aretransferred from the vibrating actuator 308 to pressure plate 312.Implantable plate assembly 314 is part of the implantable portion 306,and can be made of a ferromagnetic material that can be in the form of apermanent magnet. The implantable portion 306 generates and/or isreactive to a magnetic field, or otherwise permits the establishment ofa magnetic attraction between the external portion 304 and theimplantable portion 306 sufficient to hold the external portion 304against the skin 332 of the recipient. Accordingly, vibrations producedby the vibrating actuator 308 of the external portion 304 aretransferred from pressure plate 312 to implantable plate 316 ofimplantable plate assembly 314. This can be accomplished as a result ofmechanical conduction of the vibrations through the skin 332, resultingfrom the external portion 304 being in direct contact with the skin 332and/or from the magnetic field between the two plates 312, 316. Thesevibrations are typically transferred without a component penetrating theskin 332, fat 328, or muscular 334 layers on the head.

As can be seen, the implantable plate assembly 314 is substantiallyrigidly attached to bone fixture 318 in this example. Implantable plateassembly 314 includes through hole 320 that is contoured to the outercontours of the bone fixture 318, in this case, a bone fixture 318 thatis secured to the bone 336 of the skull. This through hole 320 thusforms a bone fixture interface section that is contoured to the exposedsection of the bone fixture 318. In an example, the sections are sizedand dimensioned such that at least a slip fit or an interference fitexists with respect to the sections. Plate screw 322 is used to secureimplantable plate assembly 314 to bone fixture 318. As can be seen inFIG. 3 , the head of the plate screw 322 is larger than the hole throughthe implantable plate assembly 314, and thus the plate screw 322positively retains the implantable plate assembly 314 to the bonefixture 318. In certain examples, a silicon layer 324 is located betweenthe implantable plate 316 and bone 336 of the skull.

But while implantable components of the passive transcutaneous boneconduction device 300 are relatively rigidly fixed to the skull of therecipient, the external components can rotate during and between cyclesof operation of the passive transcutaneous bone conduction device 300.The external components can also shift as they are typically not, e.g.,snapped in to place during operation. This rotation and/or shifting canimpact operation of, e.g., beam forming algorithms and feedbackalgorithms.

FIG. 4 is a perspective view of a direct acoustic stimulator 400B,comprising an external component 442 which is directly or indirectlyattached to the body of the recipient, and internal component 444B whichis implanted in the recipient. The recipient has an outer ear 401, amiddle ear 405 and an inner ear 407. Components of outer ear 401, middleear 405 and inner ear 407 are described below. In a fully functionalear, outer ear 401 comprises an auricle 410 and an ear canal 402. Anacoustic pressure or sound wave is collected by auricle 410 andchanneled into and through ear canal 402. Disposed across the distal endof ear canal 402 is a tympanic membrane 404 which vibrates in responseto the sound wave. This vibration is coupled to oval window or fenestraovalis (not shown) through three bones of middle ear 405, collectivelyreferred to as the ossicles. Bones of middle ear 405 serve to filter andamplify the sound wave, causing the oval window to articulate, orvibrate in response to vibration of tympanic membrane 404. Thisvibration sets up waves of fluid motion of the perilymph within cochlea441. Such fluid motion, in turn, activates tiny hair cells (not shown)inside of cochlea 441. Activation of the hair cells causes appropriatenerve impulses to be generated and transferred through the spiralganglion cells (not shown) and auditory nerve 414 to the brain (also notshown) where they are perceived as sound.

External component 442 typically comprises one or more sound inputelements, such as microphones 431, sound processing unit 424, a powersource (not shown), and an external transmitter unit (also not shown).The internal component 444B comprises internal receiver unit 432,stimulator unit 420, and stimulation arrangement 450B. Stimulationarrangement 450B is implanted in middle ear 405 and includes actuator440, stapes prosthesis 454 and coupling element 453 connecting theactuator 440 to the stapes prosthesis 454. In this example, stimulationarrangement 450B is implanted and/or configured such that a portion ofstapes prosthesis 454 abuts round window 421. It should be appreciatedthat stimulation arrangement 450B can alternatively be implanted suchthat stapes prosthesis 454 abuts an opening in horizontal semicircularcanal 426, in posterior semicircular canal 427 or in superiorsemicircular canal 428.

A sound signal is received by one or more microphones 424, processed bysound processing unit 426, and transmitted as encoded data signals tointernal receiver 432. Based on these received signals, stimulator unit420 generates drive signals that cause actuation of actuator 440. Thisactuation is transferred to stapes prosthesis 454 such that a wave offluid motion is generated in the perilymph in scala tympani. Such fluidmotion, in turn, activates the hair cells of the organ of Corti.Activation of the hair cells causes appropriate nerve impulses to begenerated and transferred through the spiral ganglion cells (not shown)and auditory nerve 414 to the brain (also not shown) where they areperceived as sound.

FIG. 4 provides an illustrative example of a direct acoustic stimulatorsystem, more specifically, a direct acoustic cochlear stimulator. Amiddle ear mechanical stimulation device (or middle ear device) can beconfigured in a similar manner, with the exception that instead of theactuator 440 being coupled to the inner ear of the recipient, theactuator is coupled to a bone of the middle ear 405. For example, theactuator can stimulate the middle ear by direct mechanical coupling viaa coupling element (e.g., similar to coupling element 453).

Referring to FIG. 5 , cochlear implant system 500 includes animplantable component 544 typically having an internalreceiver/transceiver unit 532, a stimulator unit 520, and an elongatelead 518. The internal receiver/transceiver unit 532 permits thecochlear implant system 510 to receive and/or transmit signals to anexternal device. The external device can be a button sound processorworn on the head that includes a receiver/transceiver coil and soundprocessing components. Alternatively, the external device can be just areceiver/transceiver coil in communication with a BTE device thatincludes the sound processing components and microphone. The implantablecomponent 544 includes an internal coil 536, and preferably, a magnet(not shown) fixed relative to the internal coil 536. The magnet isembedded in a pliable silicone or other biocompatible encapsulant, alongwith the internal coil 536. Signals sent generally correspond toexternal sound 513. Internal receiver unit 532 and stimulator unit 520are hermetically sealed within a biocompatible housing, sometimescollectively referred to as a stimulator/receiver unit. The magnetsfacilitate the operational alignment of the external and internal coils,enabling internal coil 536 to receive power and stimulation data fromexternal coil 530. The external coil 530 is contained within an externalportion 550. Elongate lead 518 has a proximal end connected tostimulator unit 520, and a distal end implanted in cochlea 540. Elongatelead 518 extends from stimulator unit 520 to cochlea 540 through mastoidbone 519. An intra-cochlear region 546 extends from the lead 518 andinto the cochlea 540.

In certain examples, external coil 530 transmits electrical signals(e.g., power and stimulation data) to internal coil 536 via a radiofrequency (RF) link, as noted above. Internal coil 536 is typically awire antenna coil comprised of multiple turns of electrically insulatedsingle-strand or multi-strand platinum or gold wire. The electricalinsulation of internal coil 536 is provided by a flexible siliconemolding. Various types of energy transfer, such as infrared (IR),electromagnetic, capacitive and inductive transfer, can be used totransfer the power and/or data from external device to cochlear implant.Communication of the signals between the external coil 530 and theinternal induction coil 536 can be indicative of the external device 530being in an operational position. Certain cochlear implant systems 500can also include a speaker 542 that extends into an ear canal of arecipient so as to deliver audible sounds at certain predeterminedfrequencies. Such devices, referred to as electro-acoustic implants, canalso benefit from the technologies described herein to reduce feedback.

FIG. 6 is a schematic diagram of a totally implantable cochlear implant600. In a totally implantable cochlear implant 600, all components areconfigured to be implanted under skin/tissue 602 of a recipient. Becauseall components of cochlear implant system 600 are implantable, cochlearimplant system 600 operates, for at least a finite period of time,without the need of an external device. An external device 604 can beused to charge the internal battery, to supplement the performance ofthe implanted microphone/system, or for when the internal battery nolonger functions. External device 604 can be a dedicated charger or aconventional cochlear implant sound processor. Either way, the externaldevice 604 preferably incorporates a microphone.

As noted, cochlear implant system 600 includes a main implantablecomponent 606 having a hermetically sealed, biocompatible housing 608.The technologies described herein that detect an operational positioncan be incorporated into either or both of the external device 604 andthe main implantable component 606. Disposed in main implantablecomponent 606 is a microphone 610 configured to sense a sound signal612. Microphone 610 can include one or more components to pre-processthe microphone output. As an alternative, the microphone and otheraspects of the system can be included in an upgrade or tethered moduleas opposed to in a unitary body as shown in FIG. 6 . For example, aremote microphone 610 a tethered to the main implantable component 606can be utilized.

An electrical signal 614 representing sound signal 612 detected bymicrophone 610, 610 a is provided from the microphone 610, 610 a tosound processing unit 616. Sound processing unit 616 implements one ormore speech processing and/or coding strategies to convert thepre-processed microphone output into data signals 618 for use bystimulator unit 620. Stimulator unit 620 utilizes data signals 618 togenerate electrical stimulation signals 622 for delivery to the cochleaof the recipient. In the example of FIG. 6 , cochlear implant system 600comprises stimulating lead assembly 624 for delivering stimulationsignal 622 to the cochlea.

Cochlear implant system 600 also includes a rechargeable power source626. Power source 626 can comprise, for example, one or morerechargeable batteries. As described below, power is received from anexternal device, such as external device 604, and is stored in powersource 626. The power can then be distributed to the other components ofcochlear implant system 600 as needed for operation.

Main implantable component 606 further comprises a control module 628.Control module 628 includes various components for controlling theoperation of cochlear implant 600, or for controlling specificcomponents of cochlear implant system 600. For example, controller 628can control the delivery of power from power source 626 to othercomponents of cochlear implant system 600. For ease of illustration,main implantable component 606 and power source 626 are shown separate.However, power source 626 can alternatively be integrated into ahermetically sealed housing 606 or part of a separate module coupled tocomponent 606. Magnetic sensors (not shown) are operatively connected tothe control module 628 and are described further herein (e.g., sensor330).

As noted above, cochlear implant system 600 further comprises a receiveror transceiver unit 630 that permits cochlear implant system 600 toreceive and/or transmit signals 632 to the external device 604. For easeof illustration, cochlear implant system 600 is shown having atransceiver unit 630 in main implantable component 606. In alternativearrangements, cochlear implant system 600 includes a receiver ortransceiver unit which is implanted elsewhere in the recipient outsideof main implantable component 606.

Transceiver unit 630 is configured to transcutaneously receive powerand/or data 632 from external device 604. Power 634 can also betransferred to and from the transceiver unit 630 to charge the powersource 626. Signals 636 (power, data, or otherwise) can also be sentto/from the transceiver 630, the sound processing unit 616, and othercomponents of the device as required or desired. As used herein,transceiver unit 630 refers to any collection of one or more implantedcomponents which form part of a transcutaneous energy transfer system.Further, transceiver unit 630 includes any number of component(s) whichreceive and/or transmit data or power, such as, for example a coil for amagnetic inductive arrangement, an antenna for an alternative RF system,capacitive plates, or any other suitable arrangement. Various types ofenergy transfer, such as infrared (IR), electromagnetic, capacitive andinductive transfer, can be used to transfer the power and/or data 632from external device 604 to the main implantable component 606.

As noted, transceiver unit 630 receives power and/or data 632 fromexternal device 604. In the illustrative arrangement of FIG. 6 ,external device 604 comprises a power source (not shown) disposed in anoff the ear processor, which is held in place on the recipient's headusing any of the foregoing techniques described, e.g., via a magnet (notshow) disposed in the external device 604 and another magnet (not shown)disposed in the main implantable component 606. In such embodiments, theexternal device 604 is able to rotate and shift to some degree duringoperation and in between cycles of operation of the cochlear implantsystem 600 and/or external component 604, which can have an impact on abeam forming algorithm in operation on cochlear implant system 600.Further, the presence of the external device 604 can be detected usingany of the suitable techniques described herein. Nevertheless, theexternal device shown in FIG. 6 is merely illustrative, and otherexternal devices can be alternatively used.

While specific types of auditory prostheses have been described herein,one of skill in the art will appreciate that the systems and methodsdisclosed herein can be performed using other types of auditoryprostheses. For example, the aspects described herein can be performedusing a hearing aid, middle ear implant, or other device. Other types ofdevices can also benefit from the aspects disclosed herein such as, forexample, headphones, mobile phones, wireless earpieces, etc. Operationalpositioning can vary depending on the type of device. For example,hearing aids and passive transcutaneous auditory implant lacks a snapcoupling or other type of fastener that limits its processor to a rangeof positions. Thus, the operational positioning of the sound processorfor such a device is not so limited in its range of positioning. Assuch, there can be greater changes to the effective feedback path ofsuch devices than there will be with other in which the sound processordoes snap into position, e.g., a percutaneous auditory prosthesis.

Having described various devices that can employ the aspects disclosedherein, the disclosure will now describe various methods for executingprocesses in an efficient manner. FIG. 7 is an exemplary method 700 forexecuting a process upon detecting that a device is in an operationalposition. The method 700 can be implemented using hardware, software, ora combination of hardware and software. In embodiments, the method 700can be performed by an auditory prosthesis, such as, for example, a boneconduction device, a middle ear device, a hearing aid, etc. The method700 may also be performed using a general computing device connected toand/or in communication with any of the foregoing. Flow begins atoperation 702 where a device is initialized. In one example,initializing a device includes powering on the device. As describedabove, some processes executed by the device produce better results whenthe device is in an operational position than they would if theprocesses were executed before the device is in an operational position.However, in some aspects, while such processes might not complete beforethe device is in place, parameters can be set upon initialization of thedevice at operation 702.

After initializing the device, flow continues to operation 704 where amonitoring of the device position is performed. As previously described,aspects disclosed herein relate to performing actions when a device isin an operational position. In examples, an operational position refersto the positioning of a device in a manner that the device is intendedto operate in. As an example, an operational position may be a physicallocation such as the placement of an external sound processor for animplantable auditory prosthesis within proximity of an implantedcomponent, placement of a hearing aid in a recipient's ear canal,placement of a headset on an outer ear, etc. In examples, thedetermination may be made using various components of a device such as,but not limited to, an external and/or implanted coil, and externaland/or implanted magnet, an accelerometer, a gyroscope, a magnetic fieldsensor, a proximity sensor, a button, a switch, or any other type ofcomponent capable of generating information that can be used todetermine a physical location of a device. Alternatively, an operationalposition may refer to placing the device in an operational state suchas, for example, establishing a data connection between differentoperational components of a device. For example, an auditory prosthesismay be considered to be in an operational position upon theestablishment of a data link between an external sound processor and animplanted component of the auditory prosthesis, e.g., via external andimplanted coils. Flow continues to decision operation 706 where adetermination is made as to whether the device is in an operationalposition. If the device is not in an operational position, flow branchesNO and returns to operation 704 where the method continues to monitorthe device's position.

If the device is in an operational position, flow branches YES tooperation 708. At operation 708 a process is executed. In examples, theprocess executed at operation 708 is a process that produces improvedresults, makes better determinations, or provides better outcomes whenexecuted during the correct operational placement of a device. Oneexample of such a process is initialization of a feedback algorithm.Initialization of a feedback algorithm can result in audible artifacts,particularly in systems that include a microphone or other type of inputdevice in the vicinity of an output transducer. When feedback occurs atan auditory prosthesis, the recipient of the auditor prosthesis canexperience discomfort. Feedback algorithms combat feedback by cancellingout a feedback signal using an adaptive filter. The settings applied tothe adaptive filter have an effect on the feedback reduction. The propersettings can vary depending on the positioning of the device. Because ofthis, execution of a feedback algorithm provides better results when theexecution begins when the device is in an operational positon, which isnot necessarily the same instance as when the device is initialized. Oneof skill in the art will appreciate that various different types offeedback algorithms can be practiced with the various aspects disclosedherein without departing from the spirit or scope of this disclosure.One of skill in the art will appreciate that other types of processesalso benefit from beginning execution when a device is in an operationalposition. For example, a beam forming algorithm may also benefit fromexecuting at the time that a device is placed into an operationalposition. For instance, beam forming algorithms typically focus onsounds coming from a direction in front of the recipient. If a device isstill held in the recipient's hand or otherwise not facing in a properdirection during initialization of the beam forming algorithm, thedevice might configure itself to reduce as noise speech coming from thedirection in front of the recipient. In some embodiments, before thebeam forming algorithm is initialized, the microphones of the device areconfigured to operate in omni directional mode. Changes in gain settingsare also better performed when the device is an operational position. Infurther aspects, the different processes can be executed sequentially orin parallel upon detection that the device is in place. In one example,beam forming can be executed prior to execution of the feedbackalgorithm. Because directionality can affect the feedback path, if thebeam forming is performed before feedback reduction, additional benefitscan be gained from the feedback algorithm. While the disclosuredescribes various different processes executing at operation 708, one ofskill in the art will appreciate that other types of processes can beexecuted at operation 708 without departing from the scope of thisdisclosure.

Flow continues to decision operation 710 where a determination is madeas to whether the device is still in an operational position. Asdiscussed with respect to operation 704, the determination can be basedupon the physical location of the device and/or an operating state of adevice.

As indicated herein, the device may rotate, shift or move otherwise tosome degree and still remain in an/the operational position. Typically,and depending on device type, relatively stability of the feedback path,etc., an auditory prosthesis provides 0-6 dB of additional availablegain during a fitting of the prostheses to a recipient. Further, somefeedback algorithms with phase shifting provide 10-12 dB of additionalgain without artefacts and up to 20 dB of additional gain with someartefacts. This means that in some embodiments, there is between 4-12 dBin feedback algorithm margin. So long as the movement of the device doesnot consume that margin, the device affectively remains in an/theoperational position. Moreover, in some embodiments, the operation ofthe device might be interrupted temporarily. For instance, a recipientmight lean against a wall or interrupt a feedback path between a speakerand a microphone of the device. Such actions could have a negativeimpact on operation of the device, e.g., consume the margin referred toherein. So long as the interruption is brief, e.g., less than 1 secondor within range of some other time, the device remains in theoperational positon despite the interruption. If the margin is consumedor consumed for a significant period of time, the device in someembodiments treats that as the device no longer being in the operationalposition even if, for instance, successful communications betweenexternal and internal components of the device remain.

If the device is still in an operational position, flow branches YES andreturns to operation 708 where the one or more processes continueexecution. If the device is no longer in an operational position, flowbranches NO to operation 712. At operation 712, one or more processesexecuted at operation 708 are terminated. In one example, terminatingprocesses provides for an increase in battery life for the device.Energy usage can be minimized by halting the execution of processes thatare unnecessary based upon a device's position and/or state.Additionally, halting of the one or more processes prevents the devicefrom transitioning into a sub-optimal or inoperable state. For example,the continuation of certain feedback reduction and/or beam formingalgorithms (e.g., ongoing dynamic adjustments) can result in sub-optimalsettings being applied to the device due to the fact that the device isno longer in an operational position. For example, feedback and beamforming settings applied when an auditory prosthesis is in the hand of arecipient will not produce optimal results.

Flow then continues to optional operation 714. At optional operation714, the state or settings of the device at the time the device isremoved from the operational position are saved. Saving the state orsettings can include saving any parameters or settings generated usingone or more processes executed at operation 708. Saving the state orsettings allows for the initialization of the device to the functionalstate or settings when the device was last in an operational position.This can lead to an enhanced experience for the recipient when thedevice is again placed into operation, e.g., less aggressive settingsduring initialization of the feedback algorithm.

FIG. 8 is an exemplary method 800 for executing a feedback algorithmupon detecting that a sound processor of an auditory prosthesis is in anoperational position. The method 800 can be implemented using hardware,software, or a combination of hardware and software. In embodiments, themethod 800 can be performed by an auditory prosthesis, such as, forexample, a bone conduction device, a middle ear device, a hearing aid,etc. The method 800 may also be performed using a general computingdevice connected to and/or in communication with the foregoing devices.Flow begins at operation 802 where a pre-filter may be set for afeedback algorithm. In examples, the pre-filter may be settings thatwere determined during a previous fitting process for the device. Infurther examples, the pre-filter may be settings that were in place thelast time that the device was in an operational position. In furtherembodiments, other parameters may be set at operation 802. For example,parameters related to step-size for gain increase, frequency parametersdepending upon air delay, filter dynamics, etc. may be set at operation802. Setting a pre-filter at operation 802 allows the feedback algorithmto employ slower adaptation than is possible at a later stage (e.g., atoperation 808). Slower adaptation reduces the risk of instability andreduces the chance that audible artifacts occur, thereby enhancing therecipient's experience.

Flow continues to operation 804 where monitoring of the position of thesound processor is performed. The monitoring is performed to determinewhether the sound processor is in an operational position. In oneexample, the sound processor may be in an operational position when thesound processor is in a substantially fixed location that is expectedwhile the device remains in operation. In one example, the soundprocessor may be in a substantially fixed location based upon alocational relationship of the sound processor with respect to anothercomponent of the auditory prosthesis, with respect to the recipient, orwith respect to both. In other aspects, an operational position may bedefined by a substantially fixed feedback path that is expected whilethe device is in an operational position. In still other aspects, theoperational position may be defined by feedback settings. For example,the sound processor may be in an operational position when it isdetermined that the current feedback settings are settings that tend tobe consistent from one instance of operation to the next. In oneexample, the sound processor can be determined to be in an operationalposition based upon a coil-on event. That is, if the external andinternal coils of the sound processor are within proximity to oneanother and/or upon the establishment of a data link between the coils,then it can be determined that the sound processor is in an operationalposition. In an alternate embodiment, the determination of theoperational position can be based upon the proximity of internal andexternal magnets of the auditory prosthesis. When the internal andexternal magnets are in a close proximity, then the sound processor canbe determined to be in an operational position.

Flow continues to decision operation 806 where a determination is madeas to whether the sound processor is in an operational position basedupon the monitoring performed at operation 804. If it is determined thatthe device is not in an operational positon, flow branches NO andreturns to operation 804 where continued monitoring of the soundprocessor's position is performed. If the sound processor is determinedto be in an operational position, flow branches YES to operation 808. Atoperation 808, an initial phase of a feedback algorithm is executed. Inexamples, the initial phase of the feedback algorithm can have a firstadaptation speed. The first adaptation speed can be more aggressive,e.g., faster, than an operational adaptation speed. In examples, it isbeneficial to apply a more aggressive adaptation speed during theinitial phase to quickly identify and set optimal settings for the soundprocessor. However, faster adaptation speeds increase the likelihood ofaudible artifacts. As will be discussed in further detail with respectto FIG. 9 , certain mechanisms can be employed to reduce the likelihoodof such artifacts during the initial phase. Further, the relativestability of the feedback path, which depends in part on device type,can be used to configure/select the first and/or second adaptationspeeds and adjust or set other settings or characteristics during aninitialization and/or operational phase of a feedback or otheralgorithm. For instance, the first adaptation speed can be relativelyslower for devices with a relatively stable feedback path.

After the initial phase has completed, flow continues to operation 810where an operational phase of the feedback algorithm is executed. In oneexample, the initial phase can be completed after a set amount of time.Alternatively, the initial phase can be completed upon reaching acertain state or collection of settings. For example, the initial phasecan be completed upon reaching a stable feedback loop, that is, uponreaching a consistent state or collection of settings for the feedbackalgorithm. During the operational phase, the adaptation speed of thefeedback algorithm may be reduced, that is, a less aggressive adaptationspeed can be applied. It is possible to reduce the adaptation speedbecause a stable feedback loop can be in place during the operationalphase partly through the use of a properly configured and timed initialphase. The slower adaption speed reduces the likelihood of audibleartifacts during the operation of the sound processor.

After entering the operational phase, flow continues to decisionoperation 812. At decision operation 812, a determination is made as towhether the sound processor is still in the operational position. Thedetermination can be made according to the various examples describedwith respect to operations 804 and 806. If the sound processor is stillin an operational position, flow branches YES and returns to operation810 where the operational phase of the feedback algorithm continues toexecute. However, if the sound processor is no longer in an operationalposition, then flow branches NO to operation 814. At operation 814, theexecution of the feedback algorithm is terminated. Because the soundprocessor is no longer in an operational position, any adjustments madeby the feedback algorithm may result in sub-optimal performance. Inother words, any adjustments made after the sound processor is no longerin an operational position can be invalid.

After terminating execution of the feedback algorithm, flow continues tooptional operation 816. At optional operation 816, parameters and orsettings in place at the time the sound processor was in operationalposition can be saved. Saving the parameters and or settings allows forthe initialization of the sound processor to the saved parameters and orsettings. For example, the settings saved at operation 814 can beapplied during the initialization operation 802 the next time the soundprocessor is activated. This allows for the sound processor to moreefficiently and/or less aggressively reach a stable feedback loop,which, in turn, reduces the likelihood of audible artifacts.

FIG. 9 is an exemplary method 900 for performing phased feedbackreduction. The method 900 can be implemented using hardware, software,or a combination of hardware and software. In embodiments, the method900 can be performed by an auditory prosthesis, such as, for example, amiddle ear device, a bone conduction device, a hearing aid, etc. Themethod 900 can also be performed using a general computing device. Inexamples, the method 900 can be performed during operations 508 and 510of the method 500. Flow begins at operation 902 where a reducedamplification level setting is applied. Reduction of the amplificationsetting can reduce the likelihood of audible artifacts occurring duringinitialization of a feedback algorithm. In examples, in addition tosetting a reduced amplification setting, an amplification step can beset at operation 902. The amplification step defines how quickly theamplitude of the auditory prosthesis can be altered. For example, anamplification step of 5 dB can be set. Under such circumstances, theamplification of the auditory prosthesis can be adjusted in 5 dBincrements. Other step sizes can be set without departing from thespirit of this disclosure.

Flow continues to operation 904 where a feedback algorithm is executedwith a first adaptation speed. In examples, the operation 902 can beperformed at the initialization of the feedback algorithm. Because thealgorithm is just initialized, the feedback loop is more likely to beunstable. Because of this, a faster adaptation speed can be employed toquickly stabilize the feedback loop. The first adaptation speed can befaster, e.g., more aggressive. Because a reduced amplification level wasset at operation 902, the likelihood of audible artifacts is reducedduring execution of the aggressive adaptation speed. Flow continues tooperation 906 where the amplification level is adjusted by anamplification step size. In this manner, the amplification level of theauditory prosthesis can be incrementally brought to an operationalamplification setting while continuing to perform aggressive feedbackreduction. The incremental increase reduces the likelihood of generatingan audible artifact. The amplification step size can be determined by aprior setting, for example, by a level determined during operation 902.Alternatively, the amplification step size can be dynamically determinedbased upon the status of the feedback loop.

Flow continues to decision operation 908 where a determination is madeas to whether the initial phase of the feedback algorithm has completed.In one example, the initial phase can be completed after a set amount oftime. Alternatively, the initial phase can be completed upon reaching acertain state or collection of settings. For example, the initial phasecan be completed upon reaching a stable feedback loop, that is, uponreaching a consistent state or consistent settings for the feedbackalgorithm. If the feedback algorithm is still in the initial phase, flowbranches NO and returns to operation 906 where the amplification isadjusted again by a step size and the feedback algorithm continues tooperate at a faster adaptation speed. If the initial phase hascompleted, flow branches YES to operation 910.

At operation 910, the adaptation speed of the feedback algorithm isreduced, e.g., a less aggressive adaptation speed is applied. The sloweradaption speed reduces the likelihood of audible artifacts during theoperation of the sound processor. Flow then continues to operation 912where the feedback algorithm continues to operate at the reducedadaptation speed.

FIG. 10 is an embodiment of a system 1000 in which the various systemsand methods disclosed herein can operate. The most basic components ofthe system 1000 may be included as part of an auditory prosthesis. Inalternate embodiments, a client device in communication with theauditory prosthesis, can be employed to set and/or perform the feedbackalgorithms and other processes disclosed herein. In such embodiments, aclient device, such as client device 1002, can communicate with one ormore auditory prostheses, such as auditory prosthesis 1004, via anetwork 806. In embodiments, a client device can be a remote control, alaptop, a personal computer, a smart phone, a PDA, a netbook, a tabletcomputer, a server or any other type of computing device, such as thecomputing device in FIG. 10 . In embodiments, the client device 1002 andthe auditory prosthesis 1004 may communicate via communication channel1006. Communication channel 1006 can be any type of network capable offacilitating communications between the client device 1002 and theauditory prosthesis 1004. Examples of a communication channel can be anRF connection, a Bluetooth connection, a WiFi connection, or any othertype of connection capable of transmitting instructions between clientdevice 1002 and auditory prosthesis 1004.

In embodiments, the various systems and methods disclosed herein can beperformed by an auditory prosthesis, e.g., auditory prosthesis 1004, aclient device, e.g., client device 1002, or by both the auditoryprosthesis and client device. For example, in embodiments the clientdevice may perform a method to identify a control expression andinstruct the auditory prosthesis to apply an audio setting adjustment.In such embodiments, client device 1002 can transmit instructions to theauditory prosthesis to apply an audio setting instruction viacommunication connection 1006.

Communication channel 1006, in certain embodiments, is capable ofreal-time or otherwise suitably fast transmission of, e.g., instructionsfrom client device 1002 to auditory prosthesis 1004. In suchembodiments, instructions from the client device 1002 based on itsprocessing of a control expression and related conversation is receivedin good time by the auditory prosthesis 1004. If, for instance, suchinstructions are not transmitted suitably fast, an audio settingadjustment to auditory prosthesis 1004 might not be made in time benefitthe recipient (e.g., in time for the repeat of a conversation fragmentthe recipient requested with the control expression).

The embodiments described herein can be employed using software,hardware, or a combination of software and hardware to implement andperform the systems and methods disclosed herein. Although specificdevices have been recited throughout the disclosure as performingspecific functions, one of skill in the art will appreciate that thesedevices are provided for illustrative purposes, and other devices can beemployed to perform the functionality disclosed herein without departingfrom the scope of the disclosure.

This disclosure described some embodiments of the present technologywith reference to the accompanying drawings, in which only some of thepossible embodiments were shown. Other aspects can, however, be embodiedin many different forms and should not be construed as limited to theembodiments set forth herein. Rather, these embodiments were provided sothat this disclosure was thorough and complete and fully conveyed thescope of the possible embodiments to those skilled in the art.

Although specific embodiments were described herein, the scope of thetechnology is not limited to those specific embodiments. One skilled inthe art will recognize other embodiments or improvements that are withinthe scope of the present technology. Therefore, the specific structure,acts, or media are disclosed only as illustrative embodiments. The scopeof the technology is defined by the following claims and any equivalentstherein.

What is claimed is:
 1. A computer storage medium encoding computer executable instructions that, when executed by at least one processor, perform a method comprising: determining if a device is in an operational position; and in response to determining that the device is in the operational position, starting a feedback algorithm.
 2. The computer storage medium of claim 1, wherein the feedback algorithm comprises an initial phase and an operational phase.
 3. The computer storage medium of claim 2, wherein the method further comprises applying a first feedback algorithm during the initial phase and a second feedback algorithm during the operational phase, wherein the first feedback algorithm provides quicker adaptation than the second feedback algorithm.
 4. The computer storage medium of claim 1, wherein determining if the device is in the operational position, comprises determining a location of a first component of the auditory hearing prosthesis relative to a second component of the device.
 5. The computer storage medium of claim 1, wherein determining if the device is in the operational position, comprises determining a location of the auditory hearing prosthesis relative to a recipient of the device.
 6. A prosthesis device comprising: an implanted component; an external component; at least one processor; and a memory storing computer executable instructions that, when executed by the at least one processor, cause the at least one processor to: determine if the external component is in an operational position with respect to the implanted component; and when the external component is in the operational position, execute an algorithm negatively effectible by a position of the external component relative to the operational position.
 7. The device of claim 6, wherein determining that the external component is in the operational position comprises detecting an established data link with the implanted component.
 8. The device of claim 6, wherein the implanted component comprises a magnet and the at least one processor and the memory are disposed in the external component, and wherein determining that the external component is in the operational position comprises detecting that the external component is in proximity of the magnet.
 9. The device of claim 6, wherein the implanted component comprises an internal coil, and wherein the external component comprises an external coil, and wherein determining that the external component is in the operational position comprises detecting that the external coil is in proximity to the internal coil.
 10. The device of claim 9, wherein the at least one processor and the memory are disposed in the implanted component.
 11. The computer storage medium of claim 1, wherein the device comprises an auditory device.
 12. A prosthesis device comprising at least one processor and memory storing computer executable instructions that, when executed by the at least one processor, cause the at least one processor to: determine if the prosthesis device is in an operational position; and when the prosthesis device is in the operational position, execute an algorithm to reduce the likelihood of an artifact relative to that which would otherwise be the case.
 13. The prosthesis device of claim 12, wherein the prosthesis device is an external sound processor, and wherein determining that the prosthesis device is in the operational position comprises detecting that the external sound processor is in proximity of an implanted magnet.
 14. The prosthesis device of claim 12, wherein the prosthesis device is an external sound processor, and wherein determining that the prosthesis device is in the operational position comprises detecting that the external sound processor is snapped on to a percutaneous abutment.
 15. The prosthesis device of claim 12, wherein the algorithm comprises an initial phase and an operational phase.
 16. The prosthesis device of claim 15, wherein the at least one processor is further configured to apply an aggressive feedback algorithm during the initial phase, wherein the aggressive feedback algorithm provides quicker adaptation.
 17. The prosthesis device of claim 15, wherein the at least one processor is further configured to: at the start of the initial phase, set an amplification level of the device to a reduced level; and incrementally increase the amplification level during the initial phase.
 18. The prosthesis device of claim 12, wherein the artifact is an auditory artifact.
 19. The prosthesis device of claim 15, wherein the at least one processor is further configured to apply an operational feedback algorithm during the operational phase, wherein the operational feedback algorithm provides a reduced adaptation speed.
 20. The prosthesis device of claim 12, wherein the prosthesis device is one of partially implanted in or totally external to a recipient of the prosthesis. 